Optical systems for whole eye imaging and biometry

ABSTRACT

Scanning optical beam imaging systems for imaging extended structures of an eye and providing biometry of an eye are provided. The systems include a focal system for shifting the focus of the scanning system from the front to the back of the eye. The systems provide for converging rays that can scan through the pupil of the eye, enabling scanning of the anterior and posterior segments of the eye using a common objective and a fixed working distance.

CLAIM OF PRIORITY

The present application is a continuation of U.S. patent applicationSer. No. 13/705,867 filed Dec. 5, 2012, now U.S. Pat. No. 8,864,309which claims priority to U.S. Provisional Application No. 61/566,856,filed Dec. 5, 2011, and U.S. Provisional Application No. 61/620,645,filed Apr. 5, 2012, the disclosures of which are hereby incorporatedherein by reference as if set forth in their entirety.

STATEMENT OF GOVERNMENT SUPPORT

This invention was funded in-part with government support under GrantApplication ID 1R43EY022835-01 entitled Aspheric SDOCT Imaging Systemfor Dry Eye and Cornea Diagnostics by the National Institutes of Health,National Eye Institute. The United States Government has certain rightsin this invention.

FIELD

The present inventive concept relates to imaging and, more particularly,optical coherence tomography (OCT) systems for whole eye imaging andocular biometry.

BACKGROUND

Optical coherence tomography (OCT) and, in particular, Fourier domainoptical coherence tomography (FDOCT) is a standard of care in clinicalophthalmology. FDOCT systems acquire images of translucent structuresrapidly and at high resolution, but have limited imaging depth due tooptical constraints. For these reasons, among others, FDOCT is widelyadopted for imaging of the retina where the necessary depth of field islimited, but use in refractive applications involving the entirerefractive structure of the eye remains still developing.

Low coherence interferometry (LCI), the non-scanning analog of OCT, iscommonly used in ocular biometry to measure distance between opticalsurfaces of the eye. This application is important to planning ofrefractive and cataract surgery, and to the prescription of replacementlens used in cataract surgery. These measurements are accurate andrapid, but are not typically combined with imaging and, thus, havelimitations in utility and may not fully exploit the volumetric imagingcapabilities of LCI, OCT and FDOCT.

Corneal topographers are able to measure the shape of the front, oranterior surface of the eye using the distortion of a pattern reflectedfrom the cornea. Approximations are used to compute refractiveparameters of the eye based on these front surface images.

Computational OCT has recently been applied to imaging both the frontand back surfaces of the cornea to improve the accuracy of refractivecomputations, and to couple refractive analysis with structural imaging.This technique has been applied to the cornea, but neglects the lens ofthe eye.

Wavefront aberrometry is often used to compute the functional refractivestate of the eye. This technique detects a wavefront reflected from theretina. The refractive output can be accurate, but the results do notinform the user on the origin of any aberrations or contributions torefractive power.

FIGS. 1A-1C are images illustrating a series of inner eye lid imagesobtained using Spectral Domain Ophthalmic Imaging System provided byBioptigen, Envisu™ 82300. FIG. 2 is an image obtained using a full rangeanterior segment Spectral Domain Optical Coherence Tomography (SDOCT)system with a 7.5 mm depth of view with telecentric imaging optics.FIGS. 3A through 3I are a series of images obtained using a traditionalSDOCT system with telecentric imaging optics.

A technique for obtaining an image of extended structures of the eye,suitable for computing the refractive properties of the eye andmeasuring axial and lateral distances of the eye has the potential toprovide all of the benefits of LCI, OCT, topography, and aberrometry inone consolidated instrument.

SUMMARY

Some embodiments of the present inventive concept provide scanningoptical beam imaging systems for imaging a surface with convexcurvature. The systems include a sphero-telecentric objective, wherein ascanning radius of curvature of the sphero-telecentric objective isgreater than an apical radius of curvature of the surface and less thanor equal to four times an apical radius of curvature of the surface.

In further embodiments, the sphero-telecentric objective may includelens elements arranged in four or fewer lens groups.

In still further embodiments, the sphero-telecentric objective mayinclude an aspheric optical element.

In some embodiments, the scanning optical beam imaging system may be anoptical coherence tomography imaging system.

In further embodiments, the scanning optical beam imaging system may bean input beam zoom. The input beam zoom may include an input lightsource; a positive lens group in a first position; a movable negativelens group in a second position; a movable positive lens group in athird position, wherein relative positions of the movable negative lensgroup in the second position to the positive lens group in the firstposition, and the moveable positive lens group in the third position tothe movable negative lens group in the second position control anumerical aperture and a degree of focus of the imaging system.

In still further embodiments, the scanning optical beam imaging systemmay include a telecentric scanning input. The telecentric scanning inputmay include an input light source; an input beam shaping system; a firstmirror set to scan along a first direction; a first telecentric relayconfigured to image the first mirror set to a second mirror set to scanalong a second direction orthogonal to the first direction; and anobjective that receives the telecentrically scanned input beam to aregion of a subject.

Some embodiments of the present inventive concept provide ophthalmicoptical coherence tomography imaging systems including asphero-telecentric imaging objective, wherein a scanning radius ofcurvature of the sphero-telecentric objective is greater than an apicalradius of curvature of a cornea of the eye and less than or equal tofour times an apical radius of curvature of the cornea of the eye.

In further embodiments, the sphero-telecentric objective may includelens elements arranged in four or fewer lens groups.

In still further embodiments, the sphero-telecentric objective mayinclude an aspheric optical element.

In some embodiments, the optical coherence tomography imaging system mayfurther include an input beam zoom. The input beam zoom may include aninput light source; a positive lens group in a first position; a movablenegative lens group in a second position; a movable positive lens groupin a third position, wherein relative positions of the movable negativelens group in the second position to the positive lens group in thefirst position, and the movable positive lens group in the thirdposition to the negative lens group in the second position controls anumerical aperture and a degree of focus of the imaging system.

In further embodiments, the optical coherence tomography imaging systemmay include a telecentric scanning input. The telecentric scanning inputmay include an input light source; an input beam shaping system; a firstmirror set to scan along a first direction; a first telecentric relaythat images the first mirror set to a second mirror set to scan along asecond direction orthogonal to the first direction; and an objectivethat receives the telecentrically scanned input beam to a region of asubject.

BRIEF DESCRIPTION OF THE DRAWINGS

FIGS. 1A-1C are a series of inner eye lid images obtained using SpectralDomain Ophthalmic Imaging System provided by Bioptigen, Envisu™ R2300.

FIG. 2 is an image obtained using a full range anterior segment SpectralDomain Optical Coherence Tomography (SDOCT) system with a 7.5 mm depthof view with telecentric imaging optics.

FIGS. 3A through 3I are a series of images obtained using a traditionalSDOCT system with telecentric imaging optics.

FIGS. 4A through 4C are diagrams illustrating sphero-telecentric opticalcoherence tomography (OCT) field curvature vs. cornea shape.

FIGS. 5A and 5B illustrate two optical scan head designs in accordancewith some embodiments of the present inventive concept.

FIG. 6 is a block diagram illustrating an example OCT system.

FIG. 7 is a block diagram illustrating an example OCT retinal imagingsystem.

FIG. 8 is a block diagram illustrating an example OCT cornea imagingsystem.

FIG. 9 is a block diagram illustrating a telecentric scanning system forophthalmic anterior imaging.

FIG. 10 is a block diagram illustrating a curved lens group forpath-length managed imaging of a spherical surface (sphero-telecentricimaging).

FIG. 11 is a block diagram illustrating imaging geometry forsphero-telecentric imaging in accordance with some embodiments of thepresent inventive concept.

FIG. 12 is a diagram illustrating a telecentric scanning system withfocus control, numerical aperture control and beam expansion inaccordance with some embodiments of the present inventive concept.

FIGS. 13A through 13C are a series of diagrams illustrating input beamshape control.

FIGS. 14A and 14B are a series of diagrams illustrating input beam shapecontrol in accordance with some embodiments of the present inventiveconcept.

FIGS. 15A through 15C are a series of block diagrams illustratingoperations of input beam shape control for high numerical aperture, lownumerical aperture and low numerical aperture with deep focus,respectively, in accordance with some embodiments of the presentinventive concept.

FIG. 16 is a graph illustrating zoom factor as a function of input beamzoom lens spacing in accordance with some embodiments of the presentinventive concept.

FIG. 17 is a graph illustrating input beam zoomfocal power as a functionof final lens spacing in accordance with some embodiments of the presentinventive concept.

FIG. 18 is a diagram illustrating a galvo relay lens (GRL) system inaccordance with some embodiments of the present inventive concept.

FIG. 19 is a block diagram illustrating an optical path length andtelecentricity manager in accordance with some embodiments of thepresent inventive concept.

FIG. 20 is a block diagram of a telecentricity-managed OCT imaging pathin accordance with some embodiments of the present inventive concept.

FIG. 21 is a graph illustrating sphero-telecentricity in OCT imaging inaccordance with some embodiments of the present inventive concept.

FIGS. 22A through 22C are diagrams illustrating elements ofsphero-telecentric systems having a 16 mm radius of curvature inaccordance with some embodiments of the present inventive concept.

FIGS. 23A and 23B are diagrams illustrating elements ofsphero-telecentric systems having a 12 mm radius of curvature inaccordance with some embodiments of the present inventive concept.

FIGS. 24A and 24B are diagrams illustrating elements ofsphero-telecentric systems having an 8 mm radius of curvature inaccordance with some embodiments of the present inventive concept.

FIG. 25 illustrates a sphero-telecentric system having 12 mm radius ofcurvature in accordance with some embodiments of the present inventiveconcept.

FIGS. 26A and 26B are graphs illustrating two modes of imaging using a12 mm radius of curvature sphero-telecentric system in accordance withsome embodiments of the present inventive concept.

FIG. 27 is a flowchart illustrating operations for an imaging ocularbiometer using sphero-telecentric optics in accordance with someembodiments of the present inventive concept.

FIG. 28 is a diagram illustrating an axial biometer acquisition inaccordance with some embodiments of the present inventive concept.

FIG. 29 is a flow diagram illustrating imaging both the anterior andposterior segments of the eye using sphero-telecentric optics inaccordance with some embodiments of the present inventive concept.

FIGS. 30A-30C are a series of block diagrams illustrating examplesettings for various modes in accordance with some embodiments of thepresent inventive concept.

FIG. 31 is a flow chart illustrating operations for imaging ocularbiometer using sphero-telecentric optics in accordance with someembodiments of the present inventive concept.

DETAILED DESCRIPTION

The present inventive concept will be described more fully hereinafterwith reference to the accompanying figures, in which embodiments of theinventive concept are shown. This inventive concept may, however, beembodied in many alternate forms and should not be construed as limitedto the embodiments set forth herein.

Accordingly, while the inventive concept is susceptible to variousmodifications and alternative forms, specific embodiments thereof areshown by way of example in the drawings and will herein be described indetail. It should be understood, however, that there is no intent tolimit the inventive concept to the particular forms disclosed, but onthe contrary, the inventive concept is to cover all modifications,equivalents, and alternatives falling within the spirit and scope of theinventive concept as defined by the claims. Like numbers refer to likeelements throughout the description of the figures.

The terminology used herein is for the purpose of describing particularembodiments only and is not intended to be limiting of the inventiveconcept. As used herein, the singular forms “a”, “an” and “the” areintended to include the plural forms as well, unless the context clearlyindicates otherwise. It will be further understood that the terms“comprises”, “comprising,” “includes” and/or “including” when used inthis specification, specify the presence of stated features, integers,steps, operations, elements, and/or components, but do not preclude thepresence or addition of one or more other features, integers, steps,operations, elements, components, and/or groups thereof. Moreover, whenan element is referred to as being “responsive” or “connected” toanother element, it can be directly responsive or connected to the otherelement, or intervening elements may be present. In contrast, when anelement is referred to as being “directly responsive” or “directlyconnected” to another element, there are no intervening elementspresent. As used herein the term “and/or” includes any and allcombinations of one or more of the associated listed items and may beabbreviated as “/”.

Unless otherwise defined, all terms (including technical and scientificterms) used herein have the same meaning as commonly understood by oneof ordinary skill in the art to which this inventive concept belongs. Itwill be further understood that terms used herein should be interpretedas having a meaning that is consistent with their meaning in the contextof this specification and the relevant art and will not be interpretedin an idealized or overly formal sense unless expressly so definedherein.

It will be understood that, although the terms first, second, etc. maybe used herein to describe various elements, these elements should notbe limited by these terms. These terms are only used to distinguish oneelement from another. For example, a first element could be termed asecond element, and, similarly, a second element could be termed a firstelement without departing from the teachings of the disclosure. Althoughsome of the diagrams include arrows on communication paths to show aprimary direction of communication, it is to be understood thatcommunication may occur in the opposite direction to the depictedarrows.

Although many of the examples discussed herein refer to the sample beingan eye, specifically, the retina, cornea, anterior segment and lens ofthe eye, embodiments of the present inventive concept are not limited tothis type of sample. Any type of sample that may be used in conjunctionwith embodiments discussed herein may be used without departing from thescope of the present inventive concept.

Some embodiments of the present inventive concept provide an imagingsystem that is more suited to clinically useful imaging of the cornea,the tear film, and the tissue ultrastructure of the inner eyelid,conjunctiva and sclera. Optics suited for imaging curved surfaces with awide field of view are provided. To provide such a system, the followingchallenges have been address: (1) Invert the scanned focal field tomatch the surface of the cornea; (2) Equalize the optical path lengthsso that a spherical surface is imaged to a plane at constant imagedepth; and (3) Introduce optical elements that allow such a design to becompact and cost effective.

Referring to FIGS. 4A-4C, the impact of field curvature and path lengthwith respect to cornea curvature for three different models of corneashape (A,B,C) will be discussed. The solid lines (left) are corneashape, i.e. the shape that will be imaged by traditional telecentric OCToptics. The dashed lines (left) represent the focal field of the targetoptics.

In particular, FIGS. 4A-4C illustrate Aspheric OCT Scan Field Curvaturevs. Cornea Shape. Telecentric imaging of cornea surface requires deepimaging for wide field of view (solid lines, left). Sphero-telecentricimaging reduces the required depth of view, and provides a surface imageas a deviation from spherical (right). FIG. 4A illustrates a sphericalcornea model, radius of curvature 7.5 mm; FIG. 4B illustrates aSpherical model with exponential tails; and FIG. 4C illustrates akeratonic model. The lines indicated the scanner field radius: 6 mm(----); 7.5 mm (-- . -- .--); 9 mm (-- .. -- .. --), respectively.

In traditional OCT the focal field will typically be flat or slightlycurved upwards. There are at least two ways to achieve a focal fieldmore adequately matched to outwardly curved surfaces with importantramifications. In one method, referred to herein as “Focal Inversion,”aspheric optics are used to focus further along the z axis as a functionof distance from the optical axis. The rays remain nominallytelecentric. As used herein, “telecentric” refers to chief rays thatremain substantially parallel to the originating optical axis. Using theFocal Inversion method, the resolution and image brightness at thetarget surface are substantially equalized, but the path lengths arenot; the shape of the cornea may appear as with traditional OCT, butresolution and brightness across the field of view (FOV) will beimproved. In the second method, referred to herein as“Sphero-Telecentricity,” the scanning rays are directed normal to atarget field surface, specifically to a spherical field surface. As usedherein, “normal” refers to being perpendicular to the surface of thetarget sphere. In these embodiments, the beams would be normal to atarget sphere and, therefore, there would be no refractive warping onpassing through the target surface. However, the path lengths away fromthe optical axis could be severely elongated and the surface distortionunmanageable. In the ideal case, the path lengths are equal across thefield. In such a perfectly Sphero-Telecentric OCT system, a sphericalsubject contour would appear as a flat surface at constant depth.

In FIGS. 4A-4C, the surfaced contours as imaged by a Sphero-TelecentricOCT system as graphed on the right for three model cornea shapes. Aspherical cornea (FIG. 4A) with radius of curvature larger than thescanner field curvature would appear to curve upward. A cornea withradius of curvature smaller than the scanner field curvature wouldappear to curve downward. The shape illustrated in FIG. 4B is a slightlymore realistic model of a healthy cornea and the FIG. 4C illustrates akeratoconic model. Thus, given a perfectly Sphero-Telecentric imagingsystem, the imaged shape of the cornea will be a direct map of thedeviation from sphericity; imaged in three dimensions, this surfacecontour will lend itself to immediate decomposition into Zernikecomponents. Furthermore, even for significant deviation from spherical,the entire surface of a cornea will map into a field depth half that ofthe telecentrically imaged subject, providing significant depth of fieldfor tissue imaging and evaluation using a system, such as the EnvisuR4300.

Referring now to FIGS. 5A-5B, two designs using aspheric optics areillustrated. For example, FIG. 5A illustrates a design using FocalInversion and FIG. 5B illustrates a design using Sphero-Telecentricity.The associated performance parameters the aspheric head designs forFIGS. 5A and 5B are listed in Table 1 set out below.

TABLE 1 Spot Size (um) OPL Working RMS vs FOV (mm) Variation DistanceDevice Concept Airy 0 3 5 7 9 (mm) (mm) Length (cm) Focal Inversion 13 4— 5 — 14 4.329 36 10 Sphero_telecentric 16 3 14 15 6 — 0.005 25 25

Referring to FIG. 5A, design 1 offers exceptional resolution across thesurface of a cornea (5-15 μm) in an 18 mm field of view, and a compactpackage (10 cm in length). However, the path length variation across thefield is 4.3 mm. This neither collapses a spherical target to a plane,nor is path length directly correlated to a useful function; the shapeof the image cornea could be derived from calibration of the scannedfield, but this introduces an additional complexity.

Referring to FIG. 5B, design 2 achieves the objective of path lengthequalized Sphero-Telecentricity. The path length variation across a 14mm field of view is 5 μm (0.005 mm), which is exceptional. This isaccomplished by an inventive use of aspheric imaging optics togetherwith a novel shaped path equalizing element (PEQ). The resolutionremains within 15 μm across the field. The trade-off is an increase inoptical elements and device length, at 25 cm. Various embodiments of thepresent inventive concept will be discussed below with respect to thefigures below.

FDOCT systems will now be discussed with respect to FIGS. 6 through 8 toprovide some background related to these systems. Referring first toFIG. 6, a block diagram illustrating a Fourier domain OCT system will bediscussed. As illustrated in FIG. 6, the system includes a broadbandsource 600, a reference arm 610 and a sample arm 640 coupled to eachother by a beamsplitter 620. The beamsplitter 620 may be, for example, afiber optic coupler or a bulk or micro-optic coupler without departingfrom the scope of the present invention. The beamsplitter 620 mayprovide from about a 50/50 to about a 90/10 split ratio. As furtherillustrated in FIG. 6, the beamsplitter 620 is also coupled to awavelength or frequency sampled detection module 630 over a detectionpath 606 that may be provided by an optical fiber.

As further illustrated in FIG. 6, the source 600 is coupled to thebeamsplitter 620 by a source path 605. The source 600 may be, forexample, a SLED or tunable source. The reference arm 610 is coupled tothe beamsplitter over a reference arm path 607. Similarly, the samplearm 640 is coupled to the beamsplitter 620 over the sample arm path 608.The source path 605, the reference arm path 607 and the sample arm path608 may all be provided by optical fiber.

As further illustrated in FIG. 6, the sample arm 640 may includescanning delivery optics and focal optics 660. Also illustrated in FIG.6 is the reference plane 650 and a representation of an OCT imagingwindow 670.

Referring now to FIG. 7, a block diagram of an FDOCT retinal imagingsystem will be discussed. As illustrated in FIG. 7, in an FDOCT retinalimaging system, the reference arm 710 may further include a collimatorassembly 780, a variable attenuator 781 that can be neutral density orvariable aperture, a mirror assembly 782, a reference arm variable pathlength adjustment 783 and a path length matching position 750, i.e.optical path length reference to sample. As further illustrated, thesample arm 740 may include a dual-axis scanner assembly 790 and avariable focus objective lens 791.

The sample in FIG. 7 is an eye including a cornea 795, iris/pupil 794,ocular lens 793 and retina 796. A representation of an OCT imagingwindow 770 is illustrated near the retina 796. The retinal imagingsystem relies in the optics of the subject eye, notably cornea 795 andocular lens 7, to image the posterior structures of the eye.

Referring now to FIG. 8, a block diagram illustrating a FDOCT corneaimaging system will be discussed. As illustrated therein, the system ofFIG. 8 is very similar to the system of FIG. 7. However, the objectivelens variable focus need not be included, and is not included in FIG. 8.The anterior imaging system of FIG. 8 images the anterior structuresdirectly, without reliance on the optics of the subject to focus on theanterior structures.

Referring now to FIG. 9, a diagram illustrating a general concept of atelecentric scanning system for ophthalmic anterior imaging will bediscussed. As illustrated in FIG. 9, the system 900 includes a fiberinput 901, a scanning mirror 911, a telecentric scanning lens 921,telecentric scanning beams 931 that culminate at the sample, forexample, and eye 941.

Referring now to FIG. 10, a diagram illustrating a design of a curvedlens group for path length managed imaging of a spherical surface(sphero-telecentric imaging) will be discussed. As illustrated in FIG.10, the lens group includes an objective lens set 1050/1060 and a curvedlens group 1076. As will be discussed further herein, the curved lensset 1076 may provide embodiments where the rays are more perpendicularto the surface of a curved sample. This may provide a stronger signalfor layered structures, such as the cornea.

The system of FIG. 10 may essentially flatten the structure being imagedand, therefore, provide more detailed images within the readilyachievable depth range of FDOCT systems. For example, the human eye doesnot have a uniform curvature. In particular, the diameters of portionsof the eye may vary from about 8.0 mm (for the cornea) to about 12.0 mm(for the rest of the globe). The curved lens set 1076 illustrated inFIG. 10 may provide a lens designed to form a flat image of a curvedobject, for example, the human eye. The rays are normal to the curvedsurface to allow a zero optical path difference across the entire fieldof view. The curved lens set 1076 is configured to adapt to an existingretinal imager or OCT scanner to achieve cornea and OCT imaging in aflat plane. In other words, the curved lens set 1076 or multi-elementlens may be configured to image a curved object, such as the surface ofthe cornea, onto a flat plane, such as the intermediate focus planebetween the scanning and objective lenses.

Various embodiments of the present inventive concept will now bediscussed with respect to FIGS. 11 through 31. Referring first to FIG.11, a block diagram illustrating sphero-telecentric imaging inaccordance with some embodiments of the present inventive concept willbe discussed. As illustrated therein, imaging Geometry forsphero-telecentric imaging in accordance with some embodiment discussedherein has a radius of curvature (a), which is a target radius ofcurvature for imaging; an objective diameter of the lens (b) whichprovides a clear aperture of imaging objective; a working distance (c),which is the distance from imaging objective to surface of subject, forexample, the apex of the cornea; a field of view (FOV) (s), which isangular extent or chord of the spherical surface to be imaged; and aregion of constant optical path length distance (OPLD) (e), which is asub region of the field of view over which optical path lengthuniformity is maintained.

Referring now to FIG. 12, a telecentric scanning system with focuscontrol, numerical aperture (NA) control and beam expansion inaccordance with some embodiments of the present inventive concept willbe discussed. This system may provide for a highly telecentric surgicalsystem, for example. As illustrated in FIG. 12, the telecentric imagingsystem includes a fiber input (a), which may include a single modefiber; a collimator (b); an input beam zoom (input beam shape control),which provides the ability to adjust focus and control NumericalAperture (NA); mirror axis 1 (d); a telecentric relay half 1 (e), whichis a telecentric modified-Wild-eye-piece design; a telecentric relayhalf 2 (f), which is similar to (e); a mirror axis 2, orthogonal tomirror axis 1 (g); a telecentric relay half 3 (h), which is similar to(e); a telecentric beam expander (i); an imaging lens (j), which may beachromatic doublet; and a subject, which many be an eye.

FIGS. 13A through 13C illustrate a series of diagrams illustrating aninput beam zoom (IBZ) for input beam shape control. In particular, FIG.13A illustrates a method of shaping the interrogating beam. Asillustrated therein, the collimating lens that follows the input opticalfiber is allowed to move away from collimation, indicated by the arrow ato b. This design is discussed in U.S. Pat. No. 7,843,572 to Tearney foran endoscopic delivery system. The movement of the collimating lensimpacts both focus and numerical aperture of the beam delivery withoutenough degrees of freedom to shape the beam in a sufficiently controlledmanner.

Referring now to FIG. 13B, as illustrated therein, a second moveablenegative lens is added after the first movable positive lens. Thearrangement illustrated in FIG. 13B improves the separation of focus andnumerical aperture. However, allowing movement of the initialcollimating lens in this set up adversely impacts aberrations in thedownstream system and may modulate the radiant power in the system,particularly if a small aperture truncates the beam originating in thesource or source fiber.

Referring now to FIG. 13C, as illustrated therein, a fixed collimatedbeam is used followed by a moveable positive lens. In this embodiment,only the position of the focus can be changed, there is no effect on theNA.

FIGS. 14A and 14B are a series of diagrams illustrating input beam shapecontrol in accordance with some embodiments of the present inventiveconcept. Some embodiments of the present inventive concept provide afocal system that addresses the issues discussed above with respect toFIGS. 13A through 13C in providing constant radiant power to thedownstream system, and sufficient degrees of freedom to independentlycontrol numerical aperture (NA) and focus.

Referring first to FIG. 14A, an input source or source fiber (a) isfollowed by a first positive lens (b) positioned nominally one focallength away from the source, thus collimating the source. The firstpositive lens (b) is followed by a second positive lens (c) thatprovides a first focal power to the system. The second positive lens (c)is followed by a third lens (d) that is a movable negative lens thatmodifies the power of the second positive lens (c). The negative lens(d) is followed by a fourth lens (e), which is a movable positive lensthat controls the final output of this multi-lens system.

Further embodiments of the present inventive concept provide a lensgrouping that acts a zoom system, providing magnification ordemagnification of the image of the source or source fiber into thedownstream optical system. Referring to FIG. 14B, the single mode fiber(a) is followed by a first lens system (b) having an input NA and anexit NA and input focal length and output focal length. The first lenssystem (b) is followed by movable negative lens system (d), whichfollowed by movable positive lens system (e). In one configuration theoutput of the input beam zoom is a collimated beam that is focused bydownstream optical elements. Through coordinated movement of thenegative lens system (d) and the final positive lens system (e), thenumerical aperture of the complete system may be modified withoutmodifying the degree of collimation or focus. From any such numericalaperture state, a modified focal state may be achieved by independentmovement of the final lens, the focus is modified. It will be understoodthat the method of setting numerical aperture and focus need not followthe sequential adjustment discussed above. For example a lookup tablemay be used to select the positions of the lens systems to achieve adesired combined output state. It will also be understood that in someembodiments, the lens system (b) of FIG. 14B may be substantiallyequivalent to the first and second positive lenses (b and c) of FIG.14A, and conversely that lens systems (d) and (e) may not be lenssinglets but may be more complex lenses or groups of lenses.

Referring now to FIGS. 15A through 15C, a series of block diagramsillustrating diagrams of lens positions for beam shape control for highnumerical aperture, low numerical aperture and low numerical aperturewith deep focus, respectively, in accordance with some embodiments ofthe present inventive concept will be discussed. As illustrated in FIGS.15A through 15C, Lens (a) is the first positive lens; lens (b) is thesecond negative lens; and lens (c) is the third positive lens. Thedistance between lens (a) and lens (b) will be referred to as the firstlens spacing (D1) and the distance between lens (c) and lens (b) will bereferred to as the second lens spacing (D2). The position of the lens(a) is fixed in all of FIGS. 15A through 15C. Similarly, lens (b) andlens (c) are both moveable in all of FIGS. 15A through 15C.

FIG. 15A illustrates embodiments for a high numerical aperture imagingsystem. The zoom controls the numerical aperture of the system; in acollimated application, where the final focus is determined bydownstream optics, the zoom magnification provides a magnificationbetween the entrance pupil and exit pupil. The larger thismagnification, the greater the numerical aperture of the final imagingsystem. FIG. 15B illustrates embodiments having a low numericalaperture, the first spacing D1 has increased and the second spacing D2has decreased. FIG. 15C illustrates embodiments having a low numericalaperture and deeper focus, the second spacing D2 has further decreasedand the system has been modified from a collimated state to a divergingstate.

Referring not to FIG. 16, a graph illustrating zoom factor as a functionof input beam zoom (IBZ) lens spacing in accordance with someembodiments of the present inventive concept will be discussed. As usedherein, the “input beam zoom” refers to the zoom factor as a function offirst and second lens spacing, D1 and D2 discussed with respect to FIG.15A through 15C. The zoom factor controls the numerical aperture (NA).For example, at zoom factor=1, the system is in low NA mode. As zoomfactor increases, the NA of the system increases. As discussed above,the first lens spacing (D1) is the distance to the negative lens fromthe first positive lens and the second lens spacing (D2) is the distanceto the final positive lens from the negative lens.

Referring now to FIG. 17, a graph illustrating IBZ focal power as afunction of final lens spacing in accordance with some embodiments ofthe present inventive concept will be discussed. At any zoom setting,focus may be adjusted by movement of the final lens of the IBZ (lens cof FIGS. 15A through 15C). Increasing the second lens spacing (D2)increases the focal power of the IBZ, and shortens the focal length ofthe system. Reducing the second lens spacing (D2) reduces the focalpower of the IBZ and increases the focal length of the system. It willbe noted that two degrees of freedom, lens spacing D1 and lens spacingD2, provide a continuous range of control of system numerical apertureand focus. The range of control is dependent on the available physicalspace for movement of the lenses, the respective powers of the lenses,and the downstream imaging optics, as will be understood by one skilledin the art. It will also be noted that the imaging conditions aredeterministic, and multiple modes of control may be employed to achievea desired state, including without limitation, sequential orsimultaneous movement of lens, movement according to values set in alookup table, or adjustment with feedback based on positional encodersor in response to image quality feedback.

Referring now to FIG. 18, a diagram illustrating a galvo relay lens(GRL) system in accordance with some embodiments of the presentinventive concept will be discussed. As illustrated therein, the systemincludes a two telecentric GRLs (modified Wild eyepiece), i.e. a firstGRL half (GRLH) and a second GRLH. Each GRLH includes a first positivedoublet (a) that is fixed, a positive singlet pair (b) that is fixed anda second positive doublet (c) that is fixed. The GRLs control thetelecentricity of the system. The GRL as proposed enables a very highdegree of telecentricity along two orthogonal axis. This telecentricityhas not been deployed previously in scanning beam ophthalmic imagingsystems.

Referring now to FIG. 19, a block diagram illustrating an optical pathlength and telecentricity manager in accordance with some embodiments ofthe present inventive concept will be discussed. As illustrated in FIG.19, in some embodiments of the present inventive concept, an opticalpath management objective (sphero-telecentric objective) (OPMO) isintroduced in the system after the final GRL.

Referring now to FIG. 20, a block diagram of a telecentricity-managedOCT imaging path including an OPMO in accordance with some embodimentsof the present inventive concept will be discussed. As illustrated inFIG. 20, the system includes a fiber input (a); a collimator (b); aninput beam zoom (c); a mirror axis 1 scanning a long a first axis (d); atelecentric relay half 1 (e); a telecentric relay half 2 (f); a mirroraxis 2 scanning along a second axis orthogonal to the first (g); atelecentric relay half 3 (h); an optical path managed objective (OPMP)(i); and a subject (j).

Referring now to FIG. 21, a graph illustrating sphero-telecentricity inOCT imaging in accordance with some embodiments of the present inventiveconcept will be discussed. A sphero-telecentric imaging objective willfocus normal to a spherical surface with a target radius of curvature. APath-Managed sphero-telecentric objective for OCT imaging may ensurethat the optical path length will be constant across the field of view(FOV) along the target radius of curvature.

It will be understood that it is not necessarily either desirable orpossible to perfectly match the curvature of a human eye. First, thecornea of a human eye is not perfectly spherical. Second, it isdesirable to avoid specular reflections that arise in true normalimaging of the air-to-cornea interface.

The normal eye has a nominal radius of curvature of about 8 mm at theapex, increasing towards the limbus. In some embodiments of the presentinventive concept, an imaging system is provided have a 16 mm radius ofcurvature, or 2 times the nominal apical radius of curvature. A radiusof curvature larger than the apical radius of curvature of the cornea ischosen to allow a large field of view (FOV) with a comfortable workingdistance and an objective diameter that does not interfere with thesubject physiology, for example, the brow or the nose of the subject.

Referring to FIG. 21, the cosine of the angle of incidence of theinterrogating beam onto the cornea is plotted as a function of theposition along the half field of view, normalized to the cornea radius,for different values of the ratio of the imaging radius of curvature tothe cornea radius of curvature. In some embodiments of the presentinventive concept, the imaging radius of curvature may be equal to orgreater than the apical cornea radius. In particular, the imaging radiusof curvature may be between about 1× and about 4× the apical radius ofcurvature of the cornea, or between about 1.5× and about 3× the apicalradius of curvature of the cornea in order to optimize the trade-offsdiscussed.

Referring now to FIGS. 22A through 22C, diagrams illustrating asphero-telecentric system having a 16 mm radius of curvature inaccordance with some embodiments of the present inventive concept willbe discussed. As illustrated in FIG. 22A, the sphero-telecentric systemincludes a fiber input (a); a collimator (b); an input beam zoom (c); amirror axis 1 (d); a telecentric relay half 1 (e); telecentric relayhalf 2 (f); a mirror axis 2 (g); a 16 mm sphero-telecentric objective(h); and a subject (i). In some embodiments of the present inventiveconcept, the sphero-telecentric imaging system may include a collimated(a) source followed by an input beam zoom (IBZ) (b). The beam images ona first galvo mirror (d) will scan in one direction. The first galvo (e)is telecentrically imaged onto a second galvo (f) that will scan in asecond orthogonal direction. The input source is then imaged on thesubject using the path-managed sphero-telecentric objective (h).

Referring now to FIG. 22B, embodiments of the 16 mm sphero-telecentricobjective (h) of FIG. 22A using spherical optics will be discussed. Asillustrated therein, the objective (h) includes four groups of optics inembodiments illustrated in FIG. 22B. The sphero-telecentric objectiveimaging to a 16 mm radius of curvature over a 6.4 mm field of view isprescribed using spherical (normal glass) optics. The four groupsinclude a first doublet followed by a pair of singlets and a finaldoublet. The working distance (final lens to cornea) is 30 mm. Themaximum diameter of the objective is 32.5 mm. The system images to anangle accuracy of 0.01 degree, with an optical path length consistent to0.3 μm, thus exhibiting a very high degree of sphero-telecentricity asreferenced to the 16 mm target surface.

Referring now to FIG. 22C, embodiments of the 16 mm sphero-telecentricobjective (h) of FIG. 22A using aspheric optics will be discussed. Asillustrated therein, the objective (h) includes three groups of opticsin embodiments illustrated in FIG. 22C. As illustrated therein, asphero-telecentric objective imaging to a 16 mm radius of curvature overa 6.4 mm field of view is prescribed using a combination of spherical(normal glass) and aspheric optics including elements in three groups.The groups include a first doublet followed by a double-sided asphereand a final doublet. The aspheric surfaces are mild aspheres, requiringless than 5 μm depth to remove from the sphere, a prescription fordefining and asphere as is known in the art. The working distance (finallens to cornea) is 30 mm. The maximum diameter of the objective is 33mm. The system images to an angle accuracy of 0.01 degree, with anoptical path length consistent to 0.3 μm, thus exhibiting a very highdegree of sphero-telecentricity as referenced to the 16 mm targetsurface, using fewer lens elements than the spherical optic design ofFIG. 22B.

Referring now to FIGS. 23A and 23B, diagrams illustrating asphero-telecentric system using spherical optics and having a 12 mmradius of curvature in accordance with some embodiments of the presentinventive concept. As illustrated in FIG. 23A, the 12 mmsphero-telecentric system using spherical optics includes 6 lens groups.In particular, the sphero-telecentric objective imaging to a 12 mmradius of curvature over a 5.5 mm field of view is prescribed usingspherical (normal glass) optics comprising elements in six groups. Thegroups include a first pair of doublets followed by a third doublet, afourth doublet, a singlet and a final doublet. The working distance(final lens to cornea) is about 14 mm. The maximum diameter of theobjective is about 22.6 mm. The system images to an angle accuracy of0.01 degree, with an optical path length consistent to 0.3 um.

As illustrated in FIG. 23B, a 12 mm sphero-telecentric system usingaspheric optics includes 4 lens groups, reduced from 6 in the embodimentdiscussed with respect to FIG. 23A. In particular, a sphero-telecentricobjective imaging to a 12 mm radius of curvature over a 5.5 mm field ofview is prescribed using spherical (normal glass) and aspheric opticsincludes elements in four groups. The four groups include a firstsinglet, a first doublet, a first single-sided asphere, and a finaldoublet. The aspheric surface is a mild asphere, which may require lessthan 4.0 μm depth to remove from the sphere. The working distance (finallens to cornea) is about 14.2 mm. The maximum diameter of the objectiveis about 27 mm. The system images to an angle accuracy of 0.01 degree,with an optical path length consistent to 0.3 μm.

Referring now to FIGS. 24A and 24B, diagrams illustrating asphero-telecentric system having a 8 mm radius of curvature inaccordance with some embodiments of the present inventive concept willbe discussed. As illustrated in FIG. 24A, the 8 mm sphero-telecentricsystem using spherical optics includes a complicated series of optics.In particular, a sphero-telecentric objective imaging to an 8 mm radiusof curvature over a 4.5 mm field of view is prescribed using spherical(normal glass) optics including elements in multiple groups asillustrated in FIG. 24A. The working distance (final lens to cornea) isabout 10 mm. The maximum diameter of the objective is about 19 mm. Thesystem images to an angle accuracy of 0.01 degree, with an optical pathlength consistent to 0.3 μm. The complex design illustrated in FIG. 24Ais provided to illustrate the variety of designs that may be brought tobear on the problem.

As illustrated in FIG. 24B, the 8 mm sphero-telecentric system usingaspheric optics reduces the complicated set of optics illustrated inFIG. 24A to optical elements arranged in 4 groups. In particular, asphero-telecentric objective imaging to an 8 mm radius of curvature overa 5.5 mm field of view is prescribed using spherical (normal glass) andaspheric optics comprising elements in four groups. The four groupsinclude a first doublet, a first singlet, a first single-sided asphere,and a final doublet. The aspheric surface is a mild asphere, requiringless than about 4 μm depth to remove from the sphere. The workingdistance (final lens to cornea) is about 10 mm. The maximum diameter ofthe objective is about 23 mm. The system images to an angle accuracy of0.01 degree, with an optical path length consistent to 0.2 μm. Thedegree of path length constancy in this design is better than 0.005%over the 5.5 mm field of view.

Referring now to FIG. 25, a sphero-telecentric system having a 12 mmradius of curvature defocused to image to the retina in accordance withsome embodiments of the present inventive concept will be discussed. Itwill be understood that although embodiments of FIG. 25 are discussedwith respect to a 12 mm sphere-telecentric system, embodiments of thepresent inventive concept are not limited to this configuration. Forexample, 8 mm and 16 mm sphero-telecentric are examples of other systemdesigns that can be defocused using the same techniques discussed belowwith respect to FIG. 25 without departing from the scope of the presentinventive concept.

Referring now to FIG. 25, a sphero-telecentric system can be defocusedusing, for example, an IBZ or paraxial lens inserted after the secondgalvo (EFL 263 mm˜3.8 D). A unique characteristic of thesphero-telecentric imaging system combined with the Input Beam Zoom(IBZ) is the ability to shift between imaging the anterior and posteriorsegments of the eye with a known degree of telecentricity without addingor subtracting lenses from the system.

In embodiments illustrated in FIG. 25, using a sphero-telecentric systemhaving a 12 mm radius of curvature sphero-telecentric objective, theretina is imaged across a 40 degree field of view (FOV) bycounter-intuitively shifting Lens (c) of the IBZ forward 6.5 mm relativeto the position for cornea imaging. This adds power to the IBZ, andshifts the focus backwards to an intermediate position within thesphero-telecentric objective. With sufficient increase in focusingpower, an internal conjugate forms, and this internal conjugate is thenimaged forward to the retina. For OCT imaging, the reference arm pathlength is adjusted to shift the interferometric condition from the frontof the eye to the back. In this mode of operation, the transitionbetween an anterior imaging telecentric system to a posterior imagingscan pivoting system is accomplished without the addition or subtractionof any lens element.

As discussed above, embodiments are not limited to using the IBZ. Forexample, the same or similar effect may be achieved by adding a paraxiallens to the system, for example, after the second galvo. In someembodiments, a 3.8 D lens may be used.

Referring now to FIGS. 26A and 26B, graphs illustrating two modes ofimaging using a 12 mm radius of curvature in a sphero-telecentric systemin accordance with some embodiments of the present inventive conceptwill be discussed. The sphero-telecentric design according to someembodiments of the present inventive concept may enable multipleapplication modes. For example, in a first mode, the IBZ focus controlmay be used to scan across an entire depth of an eye from cornea throughretina with a continuous motion of the IBZ front lens (lens c). In thismode, the front lens of the IBZ is moved forward sufficiently to move abeam conjugate into an interstitial space within the sphero-telecentricobjective. This conjugate is then imaged forward of thesphero-telecentric lens to a structure of the eye. As the front lens ofthe IBZ is positioned increasingly forward, increasing the optical powerof the IBZ, the internal, or interstitial, conjugate moves increasinglybackwards, and the image of this conjugate is pulled increasinglyforward with respect to the subject structure, as illustrated in FIG.26A. At maximum IBZ power, the conjugate is imaged at the cornea. Atminimum IBZ power, the conjugate is imaged at the retina. As illustratedin FIG. 26A, the function is continuous. A coordinated control of thereference arm of the OCT engine with the focus of the IBZ allowsacquisition of OCT data continuously along the length of the eye orother translucent object. In this mode, the working distance isincreased such that the subject is at a working distance greater thanthe sphero-telecentric radius of curvature. In 12 mm sphero-telecentricradius embodiments, the working distance for the eye becomes 37.5 mm.Note that this implies that the imaging is beyond the crossing point ofthe convergent beams; this system thus works primarily on-axis with alimited field of view (FOV) but is quite suitable for axial lengthassessment.

In particular embodiments, Mode 1 (FIG. 26A) may be a Depth Scan Mode. Aworking Distance in this mode is 37.5 mm (an additional 23.5 mm fromimaging position). The cornea is imaged with IBZ front lens (lens c) at15 mm; +14 D with respect to collimated position. As the second lensspacing is reduced from 15 mm to 6.2 mm (+5.8 D with respect to thecollimated IBZ), focal strength is reduced to scan from Cornea back toRetina in adult emmotropic eye. This may only work for on-axis or nearlyon-axis rays, and is a non-imaging configuration

In a second mode, the mode described for anterior segment imaging, andextension to posterior segment imaging is enabled. In this second mode,the working distance is constant as described for the sphero-telecentricimaging. With the IBZ focus set to collimation, the cornea surface isimaged. As the IBZ zoom power is reduced by pulling the front lensposition back, closer to the negative lens of the IBZ, the focusingpower of the system is reduced on interior surfaces of the anteriorsegment, such as the anterior surface of the crystalline lens may beimaged. This defocusing is insufficient to image through to the retina.To image the retina, the IBZ zoom power is increased, contrary tointuition as discussed above. This is because the conjugate is pulled tothe interstitial space of the objective, as discussed above, and thenimaged back to the retina. Posterior regions may be imaged so long asthey are posterior to the crossing of the scanning rays, by appropriatecontrol of the reference arm and IBZ zoom, as illustrated in FIG. 26B.

In particular embodiments, mode 2 (FIG. 26B) is an imaging mode. Theworking distance is 14 mm. The cornea is imaged with IBZ front lens(lens c) at 0 mm (IBZ collimated). An anterior surface of crystallinelens is imaged with IBZ front lens at −2.2 mm (−2 D wrt collimatd IBZ)).The Emmetropic retina is imaged with the IBZ front lens at 6.3 mm (+5.8D). The focus and reference arm length may be adjusted for hyperopes andmyopes, or for non-adult eyes as needed. There may be a dead zone withrespect to the IBZ front lens position where no imaging is possible.

Referring now to FIG. 27, a flowchart illustrating operations for animaging ocular biometer using sphero-telecentric optics in accordancewith some embodiments of the present inventive concept will bediscussed. The dual mode capability of the sphero-telecentric imagingsystem enables a unique and novel imaging biometer well suited to oculardiagnostics. As illustrated in FIG. 27, axial biometry is measured withthe system in depth scan mode (Mode 1 of FIG. 26A), and the measurementsderived from the axial biometry are used to image both anterior andposterior structures of the eye in the second, imaging mode.

Operations begin at block 2700 by setting a depth scan configuration.The system is aligned to the cornea; the working distance D1 (here D1refers to working distance, not to the IBZ lens spacing D1 as usedpreviously) is set to the depth scanning configuration, for example,37.5 mm; the reference arm is set to the appropriate position forimaging the cornea; and the IBZ focus is set to the collimated position(blocks 2710).

A series of scans are acquired throughout the depth (block 2715). Insome embodiments, a limited range B-scan, for example, 2 mm, is acquiredat least one time, and if multiple times they may be averaged forimproved signal-to-noise; the reference arm path length is increased bya fraction of the eye length; the IBZ focus power is increased accordingto the relationship as illustrated in FIG. 26B (blocks 2720). Operationsof blocks 2720 may be repeated, for example, a second B-scan isacquired; the reference arm step is selected to be a fraction of theindividual OCT A-scan length, for example 1/10^(th) the distance of theFDOCT scan window, so that subsequent scans may be aligned; and thisprocess is repeated until the entire eye length is mapped (blocks 2715,2720). In some embodiments, a sequence of about 100 B-scans stepped at250 μm, each comprising about 100 A-scans acquired at 32,000 A-scans persecond will be map the axial length of the eye in approximately ⅓ of asecond. With 3× averaging, the time increases to only about 1 second. At70,000 A-scans per second, the acquisition time is back below half asecond. This timing is also reasonable for stepping the IBZ lens and thereference arm using electromechanical actuators known in the arts.

The data is processed to identify structures in each B-scan thatrepresent the structures in the eye, using layer segmentationalgorithms, or using new algorithms designed for the purpose (blocks2760 and 2765). By using highly overlapping scan windows, any subjectmotion during the total scan period may be largely accounted for byregistering successive frames and comparing structural offsets comparedto the reference arm motion.

A linear data set identifying structural boundaries as a function ofaxial position is derived, and these positions may be used during theimaging phase to set the system parameters for both anterior andposterior imaging.

Referring now to FIG. 28, a diagram illustrating an axial biometeracquisition in accordance with some embodiments of the present inventiveconcept will be discussed. As illustrated in FIG. 28, the B-scans havinga width W are stacked for the entire eye length EL as a function ofdepth in the eye for the depth scanning mode to be used in ocularbiometry.

Referring now to FIG. 29, a flow diagram illustrating imaging both theanterior and posterior segments of the eye in accordance with someembodiments of the present inventive concept will be discussed. Someembodiments of the present inventive concept provide a third mode ofoperation for sphero-telecentric imaging system with input beam zoom(IBZ). The third mode of operation allows combined axial biometry andanterior and posterior imaging, through continuous exploration of thestructures of an eye from cornea through retina using a coordinatedchange of position of the two movable lenses in the IBZ to shift thefocus, together with a shift in the reference arm to coincide the OCTinterferometric imaging condition with the focus. In the third mode ofoperation the working distance is maintained at a fixed imagingdistance. In 12 mm imaging radius embodiments, the working distance isabout 14 mm. FIG. 29 illustrates a sequence of positions of the IBZlenses (negative lens b and positive lens c), the resultant interstitialconjugate, and the position of imaging this interstitial conjugate tothe subject (the subject conjugate). Thus, the entire length of the eyeis imaged as shown by the subject conjugate (dotted circle over variousportions of the eye/sample).

Referring now to FIG. 30A through C, block diagrams of asphero-telecentric systems and example settings for various modes inaccordance with some embodiments of the present inventive concept willbe discussed. As illustrated in FIG. 30A, the system includes a fiberinput (a); a collimator (b); an input beam zoom (IBZ) (c); a mirror axis1 (d); a telecentric relay half 1 (e); a telecentric relay half 2 (f); amirror axis 2 (g); an optical path managed objective (OPMO) (h); and asubject (i). As further illustrated in FIG. 30B, part (c) the input beamzoom (IBZ) is blown up and includes three lenses, a, b and c. Finally,in FIG. 30C, the OPMO or sphero-telecentric objective (STO) includesfirst through fourth lens groups, I, II, III and IV. The settings forlenses a, b and c of the IBZ (c) and the STO (i) are provided in thevarious charts of FIGS. 30A-C for modes 1 (imaging mode) and mode 3(combined imaging/biometry mode) discussed above.

Although settings for mode 2 are not provide, embodiments illustrated inFIGS. 30A-30C are applicable to mode 2 without departing from the scopeof the present inventive concept.

Referring now to FIG. 31, a flow chart illustrating operations for anImaging Ocular Biometer using sphero-telecentric optics in accordancewith some embodiments of the present inventive concept will bediscussed. The multi-mode capability of the sphero-telecentric imagingsystem enables a unique and novel imaging biometer well suited to oculardiagnostics. Operations begin at block 3100 by setting an imaging scanconfiguration. The system is aligned to the cornea; the working distanceD1 is set to the imaging scanning configuration, for example, 14 mm; thereference arm is set to the appropriate position for imaging the cornea;and the IBZ lens positions are set to is set to the cornea imagingpositions as prescribed in the table for Mode 3 of FIG. 30 (blocks3105).

Operations proceed to blocks 3107 and 3110 where a series of scans areacquired throughout the depth. In embodiments illustrated in FIG. 31,B-scans are acquired over the field of view applicable to the imagingposition, per the table of FIG. 30. Scans may be acquired one time, ormultiple times for averaging; the reference arm path length is increasedby a fraction of the eye length; and the IBZ lens settings are modifiedaccording to the table of FIG. 30. Until the entire eye is mapped.

The data is then processed to identify structures in each B-scan thatrepresent the structures in the eye, using layer segmentationalgorithms, or using new algorithms designed for the purpose (blocks3120 and 3125). By using highly overlapping scan windows, any subjectmotion during the total scan period may be largely accounted for byregistering successive frames and comparing structural offsets comparedto the reference arm motion.

A linear data set identifying structural boundaries as a function ofaxial position are derived, and these positions may be used is establishbiometric properties of the eye, including an axial eye length, andlengths to or thicknesses of major structures of the eye includingcornea thickness, anterior segment depth, crystalline lens thickness,posterior chamber depth, retinal thickness, etc. (blocks 3130 and 3135).Additionally, pathologies may be identified as a function of positionwithin the eye, measured, and unambiguously referenced to structures ofthe eye. Oct angiographic techniques, including Doppler OCT and othermethods of extracting vascular information known in the art may beapplied to discern blood flow properties of the uveal and retinalcirculatory systems of the eye.

Thus, as briefly discussed above, some embodiments of the presentinventive concept provide a system design that can serve a unifiedpurpose of imaging the ultrastructure of the inner eyelid, the meibomianducts, the tearfilm meniscus and the cornea with a single compacthandpiece. In some embodiments, the system may used to image a sphericalsurface onto a plane with less than 100 μm deviation, with a resolutionof better than 20 μm, across a 15 mm field of view. A flatness of betterthan 10 μm may be provided. The system may provide high quality, easilyinterpreted images of the inner eyelid, tear film, cornea and angle,which allow diagnostic assessment of structures relevant to dry eyedisease and cornea dystrophies.

Some embodiments of the present inventive concept provide a systemdesign that can serve to improve the imaging of curved surfaces such asthe cornea by increasing the degree of telecentricity to the curvedsurface, balanced to avoid excessive specular reflections arising fromperfect telecentricity to reflective surfaces.

Some embodiments of the present inventive concept provide a systemdesign that can serve a unified purpose of combining ocular biometrywith imaging of the anterior and posterior segments of the eye thoughone of multiple modes of measurement in the same optical system, withoutrequiring the insertion or removal of a lens from the system to switchbetween imaging modes.

Some embodiments of the present inventive concept provide for an inputbeam shaping mechanism that enables numerical aperture and focal controlthat may be extended to a range of optical beam imaging systems.

Example embodiments are described above with reference to block diagramsand/or flowchart illustrations of systems and devices. Thefunctions/acts noted in the blocks may occur out of the order noted inthe flowcharts. For example, two blocks shown in succession may in factbe executed substantially concurrently or the blocks may sometimes beexecuted in the reverse order, depending upon the functionality/actsinvolved. Moreover, the functionality of a given block of the flowchartsand/or block diagrams may be separated into multiple blocks and/or thefunctionality of two or more blocks of the flowcharts and/or blockdiagrams may be at least partially integrated.

In the drawings and specification, there have been disclosed exemplaryembodiments of the inventive concept. However, many variations andmodifications can be made to these embodiments without substantiallydeparting from the principles of the present inventive concept.Accordingly, although specific terms are used, they are used in ageneric and descriptive sense only and not for purposes of limitation,the scope of the inventive concept being defined by the followingclaims.

That which is claimed is:
 1. A scanning optical beam imaging system forsequentially imaging structures of a subject optical system anterior toand posterior to an aperture in the subject optical system, the systemcomprising: a source of optical radiation, an optical fiber and anoptical beam scanning assembly, wherein the source of optical radiationis coupled to the optical fiber in a sample path of the imaging systemand wherein the optical fiber is coupled to an input of an optical beamscanning assembly; an input lens assembly that directs a beam of opticalradiation from an optical fiber input to the beam scanning assembly; alens assembly following the beam scanning assembly that transforms ascanned beam to a set of non-parallel rays converging in object space;and a controller for setting a focus of the optical beam imaging system,the controller comprising a means to sequentially focus the scanningoptical beam to regions of the subject optical system anterior to anaperture of the subject optical system and to regions of the subjectoptical system posterior to an aperture of the subject optical system.2. The system of claim 1, wherein the scanning optical beam imagingsystem is in the sample arm of an optical coherence tomography (OCT)imaging system.
 3. The system of claim 2, wherein the optical coherencetomography imaging system is a Fourier domain optical coherencetomography (FDOCT) imaging system.
 4. The system of claim 3: wherein theoptical radiation from the source is transmitted along a source path ofthe FDOCT imaging system to a beamsplitter that divides the transmittedoptical radiation into a reference arm path and a sample arm path; andwherein an optical path length of a reference path is addressable tomatch an optical path length of the sample path as measured to a regionof focus of the imaging system.
 5. The system of claim 4: wherein thecontroller sequentially configures the imaging system to first andsecond configurations; wherein the first configuration comprises: afirst focus of the imaging system to focus on a region of the subjectoptical system anterior to an aperture of the subject optical system;and a first reference arm optical path length to match a sample arm pathlength as measured to the region of first focus; and wherein the secondconfiguration comprises: a second focus of the imaging system to focuson a region of the subject optical system posterior to an aperture ofthe subject optical system; and a second reference arm optical pathlength to match the sample arm path length as measured to the region ofsecond focus.
 6. The system of claim 5, wherein the FDOCT imaging systemis configured to acquire at least a first image in the firstconfiguration and a second image in the second configuration.
 7. Thesystem of claim 6, wherein the FDCOT imaging system is configured toacquire a plurality of images in a sequence of configurations, eachconfiguration comprising a unique focus and associated reference armpath length.
 8. The system of claim 7, wherein the plurality of imagesare acquired at a plurality of optical path lengths within the subjectoptical system, such that each sequential image has partial overlap withat least one neighboring image.
 9. The system of claim 8, wherein acombination of partially overlapping images forms a continuous set ofimages covering structures along an axis through an aperture of thesubject optical system from an anterior most region of interest to aposterior most region of interest.
 10. The system of claim 9, whereinthe subject optical system is an eye.
 11. The system of claim 10:wherein the aperture of the subject optical system is a pupil of theeye; wherein regions anterior to the aperture of the subject opticalsystem include at least one of a cornea, an anterior chamber and an irisof an eye; and wherein regions posterior to the aperture of the subjectoptical system include at least one of a posterior lens capsule, aposterior chamber, and a retina of an eye.
 12. The system of claim 6,wherein a measurement of a first structure in a first image, a secondstructure in a second image, and a difference between reference armoptical path lengths set in the first configuration and the secondconfiguration are combined to compute an optical path length between thefirst and second structures.
 13. The system of claim 12, wherein thefirst structure in the first image is an anterior or posterior surfaceof a cornea and the second structure in the second image is an anterioror posterior surface of a retina.
 14. The system of claim 13, whereinthe optical path length between the first and second structures is anoptical path length of an eye.
 15. The system of claim 1, wherein theinput lens assembly comprises a set of at least three lens groupsarranged along the optical axis between an input fiber and the beamscanning assembly, wherein the at least three lens groups comprise: afirst positive lens group in a first position; a negative lens group ina second position; and a second positive lens group in a third position;wherein a position of the negative lens group is movable along the axisbetween the first positive lens group and the second positive lensgroup; wherein a position of at least one of the first and secondpositive lens groups is movable along a same axis of motion as thenegative lens group; and wherein alterations of relative positions ofthe at least three lens groups along the optical axis determinealterations of an effective numerical aperture and an effective focallength of the imaging system.
 16. An optical coherence tomography (OCT)imaging system for sequentially imaging structures of a subject opticalsystem anterior to and posterior to an aperture, the system comprising:a source of optical radiation, an optical fiber and an optical beamscanning assembly, wherein the source of optical radiation is coupled tothe optical fiber in a sample path of the imaging system and wherein theoptical fiber is coupled to an input of the optical beam scanningassembly; an input lens assembly that directs a beam of opticalradiation from an optical fiber input to the beam scanning assembly; alens assembly following the beam scanning assembly that transforms ascanned beam to a set of non-parallel rays converging in object space;and a controller for setting focus of the OCT imaging system, thecontroller comprising a means to sequentially focus a scanning opticalbeam to regions of the subject optical system anterior to an aperture ofthe subject optical system and to regions of the subject optical systemposterior to an aperture of the subject optical system.
 17. The systemof claim 16, wherein the optical coherence tomography imaging system isa Fourier domain optical coherence tomography (FDOCT) imaging system.18. The system of claim 17: wherein the optical radiation from thesource is transmitted along a source path of the FDOCT imaging system toa beamsplitter that divides the transmitted optical radiation into areference arm path and a sample arm path; and wherein an optical pathlength of a reference path is addressable to match an optical pathlength of the sample path as measured to a region of focus of theimaging system.
 19. The system of claim 18: wherein the controllersequentially configures the imaging system to first and secondconfigurations; wherein the first configuration comprises: a first focusof the imaging system to focus on a region of the subject optical systemanterior to an aperture of the subject optical system; and a firstreference arm optical path length to match a sample arm path length asmeasured to the region of first focus; and wherein the secondconfiguration comprises: a second focus of the imaging system to focuson a region of the subject optical system posterior to an aperture ofthe subject optical system; and a second reference arm optical pathlength to match the sample arm path length as measured to the region ofsecond focus.
 20. The system of claim 19, wherein the FDOCT imagingsystem is configured to acquire at least a first image in the firstconfiguration and a second image in the second configuration.
 21. Thesystem of claim 20, wherein the FDCOT imaging system is configured toacquire a plurality of images in a sequence of configurations, eachconfiguration comprising a unique focus and associated reference armpath length.
 22. The system of claim 21, wherein the plurality of imagesare acquired at a plurality of optical path lengths within the subjectoptical system, such that each sequential image has partial overlap withat least one neighboring image.
 23. The system of claim 22, wherein acombination of partially overlapping images forms a continuous set ofimages covering structures along an axis through an aperture of thesubject optical system from an anterior most region of interest to aposterior most region of interest.
 24. The system of claim 23, whereinthe subject optical system is an eye.
 25. The system of claim 24:wherein the aperture of the subject optical system is a pupil of theeye; wherein regions anterior to the aperture of the subject opticalsystem include at least one of a cornea, an anterior chamber and an irisof an eye; and wherein regions posterior to the aperture of the subjectoptical system include at least one of a posterior lens capsule, aposterior chamber, and a retina of an eye.
 26. The system of claim 20,wherein a measurement of a first structure in a first image, a secondstructure in a second image, and a difference between reference armoptical path lengths set in the first configuration and the secondconfiguration are combined to compute an optical path length between thefirst and second structures.
 27. The system of claim 26, wherein thefirst structure in the first image is an anterior or posterior surfaceof a cornea and the second structure in the second image is an anterioror posterior surface of a retina.
 28. The system of claim 27, whereinthe optical path length between the first and second structures is anoptical path length of an eye.
 29. The system of claim 16, wherein theinput lens assembly comprises a set of at least three lens groupsarranged along the optical axis between an input fiber and the beamscanning assembly, wherein the at least three lens groups comprise: afirst positive lens group in a first position; a negative lens group ina second position; and a second positive lens group in a third position;wherein a position of the negative lens group is movable along the axisbetween the first positive lens group and the second positive lensgroup; wherein a position of at least one of the first and secondpositive lens groups is movable along a same axis of motion as thenegative lens group; and wherein alterations of relative positions ofthe at least three lens groups along the optical axis determinealterations of an effective numerical aperture and an effective focallength of the imaging system.
 30. An optical coherence tomography (OCT)imaging system for sequentially imaging structures of an eye, the systemcomprising: a source of optical radiation, an optical fiber and anoptical beam assembly, wherein the source of optical radiation iscoupled to the optical fiber in a sample path of the imaging system andwherein the optical fiber is coupled to an input of the optical beamscanning assembly; an input lens assembly that directs a beam of opticalradiation from an input of the optical fiber to the beam scanningassembly; a lens assembly following the beam scanning assembly thattransforms the scanned beam to a set of non-parallel rays converging inobject space; and a controller for setting the focus of the OCT imagingsystem, the controller comprising a means to sequentially focus thescanning optical beam to regions of the eye anterior to the pupil of theeye and to regions of the eye posterior to the pupil of the eye.
 31. Thesystem of claim 30, wherein the optical coherence tomography imagingsystem is a Fourier domain optical coherence tomography (FDOCT) imagingsystem.
 32. The system of claim 31: wherein the optical radiation fromthe source is transmitted along a source path of the FDOCT imagingsystem to a beamsplitter that divides the transmitted optical radiationinto a reference arm path and a sample arm path; and wherein an opticalpath length of a reference path is addressable to match an optical pathlength of the sample path as measured to a region of focus of theimaging system.
 33. The system of claim 32: wherein the controllersequentially configures the imaging system to first and secondconfigurations; wherein the first configuration comprises: a first focusof the imaging system to focus on a region of the eye anterior to thepupil of the eye; and a first reference arm optical path length to matcha sample arm path length as measured to the region of first focus; andwherein the second configuration comprises: a second focus of theimaging system to focus on a region of the eye posterior to the pupil ofthe eye; and a second reference arm optical path length to match thesample arm path length as measured to the region of second focus. 34.The system of claim 33, wherein the FDOCT imaging system is configuredto acquire at least a first image in the first configuration and asecond image in the second configuration.
 35. The system of claim 34,wherein the FDCOT imaging system is configured to acquire a plurality ofimages in a sequence of configurations, each configuration comprising aunique focus and associated reference arm path length.
 36. The system ofclaim 35, wherein the plurality of images are acquired at a plurality ofoptical path lengths within the subject optical system, such that eachsequential image has partial overlap with at least one neighboringimage.
 37. The system of claim 36, wherein a combination of partiallyoverlapping images forms a complete set images from an anterior mostregion of interest to a posterior most region of interest.
 38. Thesystem of claim 34, wherein a measurement of a first structure in afirst image, a second structure in a second image, and a differencebetween reference arm optical path lengths set in the firstconfiguration and the second configuration are combined to compute anoptical path length between the first and second structures.
 39. Thesystem of claim 38, wherein the first structure in the first image is ananterior or posterior surface of a cornea and a second structure in thesecond image is an anterior or posterior surface of a retina.
 40. Thesystem of claim 30, wherein the input lens assembly comprises a set ofat least three lens groups arranged along the optical axis between aninput fiber and the beam scanning assembly, wherein the at least threelens groups comprise: a first positive lens group in a first position; anegative lens group in a second position; and a second positive lensgroup in a third position; wherein a position of the negative lens groupis movable along the axis between the first positive lens group and thesecond positive lens group; wherein a position of at least one of thefirst and second positive lens groups is movable along a same axis ofmotion as the negative lens group; and wherein alterations of relativepositions of the at least three lens groups along the optical axisdetermine alterations of an effective numerical aperture and aneffective focal length of the imaging system.
 41. An optical coherencetomography (OCT) imaging system for sequentially imaging structures ofan eye, the system comprising: a source of optical radiation, an opticalfiber and a optical beam scanning assembly, wherein the source ofoptical radiation is coupled to the optical fiber in a sample path ofthe imaging system and wherein the optical fiber is coupled to an inputof the optical beam scanning assembly; an input lens assembly thatdirects a beam of optical radiation from the optical fiber input to thebeam scanning assembly; a lens assembly following the optical beamscanning assembly that transforms the scanned beam to a set of parallelor non-parallel rays directed towards a subject eye in object space; acontroller for setting the focus of the OCT imaging system, thecontroller comprising a means to sequentially focus the scanning opticalbeam to regions of the eye anterior to the pupil of the eye and toregions of the eye posterior to the pupil of the eye.
 42. The system ofclaim 41, wherein the optical coherence tomography imaging system is aFourier domain optical coherence tomography (FDOCT) imaging system. 43.The system of claim 42: wherein the optical radiation from the source istransmitted along a source path of the FDOCT imaging system to abeamsplitter that divides the transmitted optical radiation into areference arm path and a sample arm path; and wherein an optical pathlength of a reference path is addressable to match an optical pathlength of the sample path as measured to a region of focus of theimaging system.
 44. The system of claim 43: wherein the controllersequentially configures the imaging system to first and secondconfigurations; wherein the first configuration comprises: a first focusof the imaging system to focus on a region of the eye anterior to thepupil of the eye; and a first reference arm optical path length to matcha sample arm path length as measured to the region of first focus; andwherein the second configuration comprises: a second focus of theimaging system to focus on a region of the eye posterior to the pupil ofthe eye; and a second reference arm optical path length to match thesample arm path length as measured to the region of second focus. 45.The system of claim 44, wherein the FDOCT imaging system is configuredto acquire at least a first image in the first configuration and asecond image in the second configuration.
 46. The system of claim 45,wherein the FDCOT imaging system is configured to acquire a plurality ofimages in a sequence of configurations, each configuration comprising aunique focus and associated reference arm path length.
 47. The system ofclaim 46, wherein the plurality of images are acquired at a plurality ofoptical path lengths within the subject optical system, such that eachsequential image has partial overlap with at least one neighboringimage.
 48. The system of claim 47, wherein a combination of partiallyoverlapping images forms a complete set images from an anterior mostregion of interest to a posterior most region of interest.
 49. Thesystem of claim 45, wherein the first image acquired in the firstconfiguration and the second image acquired in the second configurationare registered and combined to create a third image comprising regionsof the eye imaged in both the first and second configurations.
 50. Thesystem of claim 49, wherein a measurement of a first structure in afirst image, a second structure in a second image, and a differencebetween reference arm optical path lengths set in the firstconfiguration and the second configuration are combined to compute anoptical path length between the first and second structures.
 51. Thesystem of claim 50, wherein the first structure in the first image is ananterior or posterior surface of a cornea and a second structure in thesecond image is an anterior or posterior surface of a retina.
 52. Thesystem of claim 45, wherein a first image acquired in a firstconfiguration and a second image acquired in a second configuration areregistered and combined to create a third image comprising regions ofthe eye imaged in both the first and second configurations.
 53. Thesystem of claim 41, wherein the input lens assembly comprises a set ofat least three lens groups arranged along the optical axis between aninput fiber and the beam scanning assembly, wherein the at least threelens groups comprise: a first positive lens group in a first position; anegative lens group in a second position; and a second positive lensgroup in a third position; wherein a position of the negative lens groupis movable along the axis between the first positive lens group and thesecond positive lens group; wherein a position of at least one of thefirst and second positive lens groups is movable along a same axis ofmotion as the negative lens group; and wherein alterations of relativepositions of the at least three lens groups along the optical axisdetermine alterations of an effective numerical aperture and aneffective focal length of the imaging system.